Segmented catheter for tissue ablation

[0001] This application is a Continuation-In-Part of U.S. Non-Provisional Patent Application entitled “Triaxial Antenna for Microwave Tissue Ablation” filed Apr. 29, 2004 and assigned U.S. application Ser. No. 10/834,802, now U.S. Pat. No. 7,101,369, the entire disclosure of which is hereby herein incorporated by reference.

[0002] This application further claims priority to U.S. Provisional Patent Applications entitled “Segmented Catheter for Tissue Ablation” filed May 10, 2005 and assigned U.S. application Ser. No. 60/679,722; “Microwave Surgical Device” filed May 24, 2005 and assigned U.S. application Ser. No. 60/684,065; “Microwave Tissue Resection Tool” filed Jun. 14, 2005 and assigned U.S. application Ser. No. 60/690,370; “Cannula Cooling and Positioning Device” filed Jul. 25, 2005 and assigned U.S. application Ser. No. 60/702,393; “Intralumenal Microwave Device” filed Aug. 12, 2005 and assigned U.S. application Ser. No. 60/707,797; “Air-Core Microwave Ablation Antennas” filed Aug. 22, 2005 and assigned U.S. application Ser. No. 60/710,276; and “Microwave Device for Vascular Ablation” filed Aug. 24, 2005 and assigned U.S. application Ser. No. 60/710,815; the entire disclosures of each and all of these applications are hereby herein incorporated by reference.

[0003] This application is related to co-pending U.S. Non-Provisional Patent Application entitled “Triaxial Antenna for Microwave Tissue Ablation” filed Apr. 29, 2004 and assigned U.S. application Ser. No. 10/834,802; and to U.S. Provisional Patent Applications entitled “Segmented Catheter for Tissue Ablation” filed May 10, 2005 and assigned U.S. application Ser. No. 60/679,722; “Microwave Surgical Device” filed May 24, 2005 and assigned U.S. application Ser. No. 60/684,065; “Microwave Tissue Resection Tool” filed Jun. 24, 2005 and assigned U.S. application Ser. No. 60/690,370; “Cannula Cooling and Positioning Device” filed Jul. 25, 2005 and assigned U.S. application Ser. No. 60/702,393; “Intralumenal Microwave Device” filed Aug. 12, 2005 and assigned U.S. application Ser. No. 60/707,797; “Air-Core Microwave Ablation Antennas” filed Aug. 22, 2005 and assigned U.S. application Ser. No. 60/710,276; and “Microwave Device for Vascular Ablation” filed Aug. 24, 2005 and assigned U.S. application Ser. No. 60/710,815; the entire disclosures of each and all of these applications are hereby herein incorporated by reference.

[0004] The present disclosure relates to medical instruments for ablating tissue.

[0005] Radiofrequency (RF) ablation is now being used for minimally invasive focal destruction of malignant tumors. Microwave ablation has many advantages over RF ablation, but has not been extensively applied clinically due to the large probe size (14 gauge) and relatively small zone of necrosis (1.6 cm in diameter) [Seki T, Wakabayashi M, Nakagawa T, et al. Ultrasonically guided percutaneous microwave coagulation therapy for small hepatocellular carcinoma. Cancer 1994;74:817-825] that is created by the only commercial device (Microtaze, Nippon Shoji, Osaka, Japan. 2.450 MHz, 1.6 mm diameter probe, 70 W for 60 seconds). The large probe size would not be compatible with percutaneous use in the chest, and would only be used with caution in the abdomen.

[0006] The basis of this invention is the resonant monopole antenna resulting from exposing a length of the center conductor equal to an electrical length equal to (2n−1)λ/4, where n=1,2 . . . 10, and is typically n=1. In this case, the electric field peaks at the end of the exposed center conductor, and is ideally at a minimum where the outer conductor terminates (FIG. 1).

[0007] The volumetric shape of the electric field lines will roughly define the zone of necrosis when a resonant coaxial probe is used as an ablation tool. More precisely, the cross product of electric and magnetic field lines determines the power available to deposit into the tissue surrounding the probe tip.

[0008] As an example, given the high dielectric constant of liver tissue (ε_r=43.03), the quarter-wave length of the center conductor protrusion for resonance at 2.45 GHz would be 4.66 mm, severely limiting the zone of necrosis. A three-quarter wave long protrusion (approximately 14 mm in physical length), which can be extended by multiple half-wavelengths is preferable.

[0009] The protrusion of the outer conductor of a coaxial line is also set to (2n−1)λ/4, where n=1,2 . . . , and is not necessarily the same amount as the inner conductor (FIG. 2). This enforces the zero-electric field boundary condition on the coaxial outer conductor, which becomes the “middle conductor.”

[0010] A near-field antenna structure is described that is an effective delivery tool for radiofrequency (RF) and microwave power to achieve coagulative necrosis in metastatic tumors while reducing or eliminating thermal conduction along the structure. This tool is a probe small enough to be used safely virtually anywhere in the neck, chest, abdomen, and pelvis, and be guided by computerized tomography (CT) or ultrasonic imaging.

[0011] This structure is resonant at a frequency of interest (a drive frequency), typically one falling in the Industrial, Scientific, and Medical (ISM) band, covering approximately 800 MHz to 6 GHz, where efficient sources of ablative power (e.g. >5 watts output) are available. The antenna structure is comprised of one or more resonant sections of coaxial, triaxial or multi-axial transmission line, forming a multi-section filter that passes the drive frequency with essentially no loss, but is incapable of efficiently conducting power at other frequencies. At the distal end, the interior conductor(s) extend from the more exterior conductors in a telescoping fashion at lengths that are resonant at the drive frequency when the catheter is inserted into the tissue to be ablated.

[0012] A particular object of the present invention is to limit the conductive path for heat generated both at the ablation site and along the filter sections so that heat travel from the distal end of the catheter to the proximal end is minimized or eliminated. By segmenting the catheter into one or more divisions, each division itself being a resonant length, electric-field coupling between adjacent segments can be preserved while interrupting the path for thermal conduction. The segmented catheter is reinforced with non-conducting materials in the gaps between segments, as well as (optionally) with a stiff inner conductor wire, thus preserving mechanical stability needed for insertion.

[0013] The preferred embodiment is a resonant coaxial, triaxial or multiaxial structure whose resonant lengths are set 2.45 GHz in the tissue of interest; the catheter can be readily impedance-matched to the tissue by adjusting the length of its coaxial center conductor with respect to its shield, which itself can fit inside one or more introducer needles of total diameter less than 12 gauge. Impedance matching to tissue is done iteratively, using a RF or microwave network analyzer to achieve a low power reflection coefficient. Because its microwave reflection coefficient is low (typically −40 dB or better), the catheter can deliver ˜100 W of power to the tissue with minimal heating of the catheter shaft, creating focal zones of coagulative necrosis >3 cm in diameter in fresh bovine liver. To achieve high power economically, we can use a magnetron power supply, with a waveguide-to-coaxial transition and a dual-directional coupler to measure incident and reflected power during the experiment.

[0014] To achieve larger zones of necrosis, multiple triaxial probes can be deployed using either a switch or power splitter to distribute the RF or microwave power.

[0015] Numerous other advantages and features of the disclosure will become readily apparent from the following detailed description, from the claims and from the accompanying drawings in which like numerals are employed to designate like parts throughout the same.

[0020] While the invention is susceptible of embodiment in many different forms, there is shown in the drawings and will be described herein in detail one or more embodiments of the present disclosure. It should be understood, however, that the present disclosure is to be considered an exemplification of the principles of the invention, and the embodiment(s) illustrated is/are not intended to limit the spirit and scope of the invention and/or the claims herein.

Segmented Resonant Catheter

[0021] According to FIG. 3, the segmented resonant catheter consists of an outer sheath (10) and subsequent inner conductors (14) and (16), with a triaxial design as the preferred embodiment, though multi-axial designs are also contemplated within the scope of the invention. Conjoining the metallic resonant segments (10) and (14) [and optionally (16)] are dielectric bridges (12) whose thickness and permittivities are set to result in resonance at the drive frequency in the tissue of interest; the drive frequency in the preferred embodiment is 2.45 GHz.

[0022] These dielectric bridges (12) are comprised of epoxy, ceramic, Teflon, delrin, or other suitable materials, and with appropriate internal stiffening from dielectric sleeves, can even be air.

Results from Segmented Resonant Catheter

[0023] A principal object of the present invention is to reduce thermal conduction along the catheter while preserving or even enhancing the microwave resonance that minimizes reflected microwave power. This is done by separating the outer conductors (and optionally, the center conductor) of the catheter into one or more segments of a resonant length (typically λ/2), starting from the distal end of the catheter, using a dielectric bridge (resin, ceramic, etc) for mechanical stability.

[0024] Additional half-wavelength segments along catheter would further improve thermal isolation.

Testing of a Prototype Small Diameter Triaxial Microwave Catheter

[0025] The applied power ranged from 25 W to 50 W with durations of up to 120 s. Reflected powers were at most −14 dB (i.e. <0.05) of the incident power, and usually −20 dB (0.01 of the incident power). The catheter temperature above the treatment area was only slightly warm to the touch, confirming that almost all the incident power was deposited into the tissue. The reason for this low reflected power is primarily due to careful tuning of the center conductor length (L2 in FIG. 2). This was accomplished by inserting the catheter into liver tissue and measuring the microwave reflection coefficient at 2.45 GHz using a calibrated Hewlett-Packard 8720D vector network analyzer. By trimming length L2 and noting the shift of the fundamental 3λ/4 resonance, small-signal reflected power was <−25 dB. Variation from this value is expected under the large-signal conditions of ablation, as tissue properties change during the procedure.

[0026] It is to be understood that the embodiment(s) herein described is/are merely illustrative of the principles of the present invention. Various modifications may be made by those skilled in the art without departing from the spirit or scope of the claims which follow.